Preparation process and application of Zn-Cu alloy based on deformation regulation

Abstract

This invention relates to a Zn-Cu alloy preparation process and its application based on controlled deformation, relating to the field of biomedical materials, particularly zinc alloys. The process involves melting Zn-Cu ingots and calcium carbonate at 450-500°C to obtain a melt, which is then cast using a semi-continuous casting process to obtain a Zn-Cu alloy ingot. After homogenization treatment, the Zn-Cu alloy ingot is then rotary forged with a total deformation of 64%-98% to obtain the Zn-Cu alloy. This invention, through a total rotary forging deformation of 64%-98%, utilizes the grain refinement effect induced by the large deformation, significantly improving the alloy's yield strength, tensile strength, and elongation at break, while simultaneously increasing the corrosion uniformity of the zinc-copper alloy, achieving a precise match between mechanical properties and the degradation rate of the zinc alloy.

Description

Technical Field

[0001] This invention belongs to the field of biomedical materials, particularly the field of zinc alloys, and specifically relates to a Zn-Cu alloy preparation process and its application based on the regulation of deformation. Background Technology

[0002] In the field of biodegradable orthopedic implant materials, Zn-Cu alloys have attracted much attention due to their excellent biocompatibility and degradation properties. However, their poor room-temperature plastic processing capability severely restricts their practical application. Conventional room-temperature pressure processing methods are difficult to use effectively to prepare these alloys, mainly because they are prone to brittle fracture and cannot achieve the desired forming effect and mechanical property matching through traditional processes such as rolling and extrusion. Although rotary forging provides a feasible way to solve the problem of low room-temperature plasticity of zinc alloys, its existing process parameters and deformation mechanisms still have significant limitations in controlling the mechanical and degradation properties of the alloys, making it difficult to meet the stringent requirements of implant materials.

[0003] From a mechanical property perspective, existing rotary forging processes tend to result in insufficient deformation uniformity in zinc alloys. The mismatch between the deformation per pass and the axial feed rate can cause turbulent metal flow, leading to localized brittle fractures in the workpiece. The strong texture formed by rotary forging inhibits grain boundary sliding. While it can improve strength by refining grains, this often comes at the cost of ductility, making it difficult to achieve a synergistic optimization of strength and ductility. This is especially true for Zn-Cu alloys, where the second phase (such as CuZn5) easily forms a coarse or continuous network structure during deformation, further exacerbating brittleness.

[0004] Regarding degradation performance, existing rotary forging processes lack effective control over the corrosion behavior of zinc alloys. The grain refinement and increased dislocation density resulting from deformation accelerate initial corrosion, while the microstructural differences between the core and surface easily lead to uneven localized corrosion, causing fluctuations in the degradation rate. Simultaneously, the process parameters do not adequately control the distribution of the second phase. If phases such as CuZn5 are unevenly dispersed, a corrosion galvanic effect can occur, triggering intergranular corrosion or locally accelerated degradation, making it difficult to match the dynamic requirements of the bone healing cycle.

[0005] In summary, the existing rotary forging process has significant shortcomings in matching the mechanical properties and degradation properties of zinc alloys, and there is an urgent need to develop a more suitable process system to meet the application requirements of biodegradable orthopedic implant materials. Summary of the Invention

[0006] The purpose of this invention is to provide a Zn-Cu alloy preparation process and its application based on the control of deformation amount. By controlling the deformation amount, it is expected to solve the problem of mismatch between the mechanical properties and degradation properties of zinc alloys in the rotary forging process.

[0007] The present invention achieves the above objectives through the following technical solutions:

[0008] A Zn-Cu alloy preparation process based on controlled deformation includes the following steps:

[0009] (1) Zn-Cu ingot and calcium carbonate are melted at 450-500℃ to obtain a melt, and then cast using a semi-continuous casting process to obtain Zn-Cu alloy ingot;

[0010] (2) After homogenizing the Zn-Cu alloy ingot, the Zn-Cu alloy ingot is then subjected to rotary forging. The total deformation of the rotary forging is 64%-98%, and a Zn-Cu alloy is obtained.

[0011] As a further optimization of the above invention, in step (1), the Zn-Cu ingot is one of Zn-2Cu alloy, Zn-3Cu alloy, and Zn-4Cu alloy.

[0012] As a further optimization of the above invention, in step (1), the amount of calcium carbonate used is 2%-4% of the mass of the Zn-Cu ingot.

[0013] As a further optimization of the above invention, in step (2), the Zn-Cu alloy ingot is homogenized in a resistance furnace, and the homogenization process is 200-300℃ / 24h.

[0014] As a further optimization of the above invention, in step (2), after homogenization, the oxidation and dirt on the surface of the Zn-Cu alloy ingot are removed by sandpaper or grinding wheel, and then acidified, and hot-dip galvanized on the surface of the Zn-Cu alloy ingot.

[0015] As a further optimization of the above invention, the hot-dip galvanizing specifically involves immersing a Zn-Cu alloy ingot in a zinc plating solution at 220-330°C for 10-15 minutes.

[0016] As a further optimization of the above invention, the zinc plating solution is composed of ZnO, NaOH and water, with a pH of 8-10.

[0017] As a further optimization of the above invention, the process parameters of the rotary forging are: temperature 100-300℃, conical feed angle 10°-21.67°, friction coefficient 0.1-0.3, axial feed speed 3-20mm / s, deformation per pass 20%-40%, and 2-3 passes.

[0018] This invention also provides the application of the Zn-Cu alloy prepared by the above-described process in the preparation of bioactive implantable devices, including its application in the preparation of orthopedic implantable devices and bioactive membranes / patches.

[0019] The orthopedic implant body includes at least one of bone plates, bone screws, bone tissue repair scaffolds, intramedullary nails, bone sheaths, or spinal fixation devices; the bioactive membrane includes at least one of guiding bone regeneration membranes, guiding tissue regeneration membranes, or oral barrier membranes; and the bioactive patch includes at least one of hernia patches or fistula patches.

[0020] The beneficial effects of this invention are as follows:

[0021] (1) By using a total forging deformation of 64%-98%, the grain refinement effect (synergistic effect of dynamic recrystallization and dislocation strengthening) caused by large deformation can be utilized to significantly improve the yield strength, tensile strength and fracture elongation of the alloy. At the same time, the mechanical properties and the degradation rate of zinc alloy can be precisely matched to meet the dual requirements of material mechanical load-bearing capacity and degradation cycle in different scenarios.

[0022] (2) The calcium carbonate added during the smelting process effectively improves the corrosion uniformity of the alloy, avoids localized excessively rapid corrosion or corrosion stagnation, and enables the alloy to maintain a stable corrosion rate during service or degradation, thereby improving the consistency and reliability of material properties.

[0023] (3) The coating formed by hot-dip galvanizing gives the alloy surface higher chemical stability, wear resistance and hardness, while strengthening the interfacial compatibility between the coating and the substrate, reducing the risk of interfacial peeling, extending the service life of the material and broadening its application range in complex environments. Attached Figure Description

[0024] Figure 1 Stress-strain curves for room temperature tensile engineering of zinc-copper alloys (Zn-2Cu, Zn-3Cu, Zn-4Cu) with different deformation amounts;

[0025] Figure 2 Fracture morphology of Zn-2Cu after room temperature tensile testing with different deformation amounts: (a): 36% (b): 64% (c): 84%;

[0026] Figure 3 Fracture morphologies of Zn-3Cu after room temperature tensile testing with different deformation amounts: (a) 36%; (b) 64%; (c) 84%.

[0027] Figure 4 Potential dynamic polarization curves of zinc-copper alloys with different deformation amounts in simulated body fluid;

[0028] Figure 5 Microstructure of Zn-2Cu samples with different deformations after immersion for 3 days: (a) 36%; (b) 64%; (c) 84%.

[0029] Figure 6Microstructures of zinc-copper alloy samples with different additives after immersion for 3 days: (a) Zn-2Cu(CaCO3); (b) Zn-2Cu(CaO); (c) Zn-2Cu-0.2Ca; (d) Zn-2Cu. Detailed Implementation

[0030] The present application will now be described in further detail with reference to the accompanying drawings. It should be noted that the following specific embodiments are only used to further illustrate the present application and should not be construed as limiting the scope of protection of the present application. Those skilled in the art can make some non-essential improvements and adjustments to the present application based on the above application content.

[0031] I. Explanation

[0032] (1) Zn-Cu ingots include Zn-2Cu alloy, Zn-3Cu alloy, Zn-4Cu alloy and Zn-0.2Cu alloy.

[0033] The raw materials for preparing Zn-Cu ingots are industrial pure zinc and industrial pure copper. Melting is carried out in a graphite crucible, with a No. 5 covering agent continuously sprayed during the stirring process to reduce oxidation loss of the melt. Hydrogen gas is then introduced for impurity removal and refining. The settling process is protected with a mixture of SF6 and CO2 gas. After settling, a semi-continuous casting process is used, employing a copper crystallizer to obtain Zn-Cu ingots (round ingots) with a diameter of 90 mm and a length of approximately 1500 mm.

[0034] (2) At least one embodiment of the present invention discloses a Zn-Cu alloy preparation process based on controlled deformation, comprising the following steps:

[0035] (1) Zn-Cu ingot and calcium carbonate are melted at 450-500℃ to obtain a melt, and then cast using a semi-continuous casting process to obtain Zn-Cu alloy ingot.

[0036] (2) After homogenizing the Zn-Cu alloy ingot, the Zn-Cu alloy ingot is then forged by rotary forging. The total deformation of the rotary forging is 64%-98%, and the Zn-Cu alloy is obtained.

[0037] In step (1), the Zn-Cu ingot is one of Zn-2Cu alloy, Zn-3Cu alloy, Zn-4Cu alloy, or Zn-0.2Cu alloy.

[0038] In step (1), the amount of calcium carbonate used is 2%-4% of the mass of the Zn-Cu ingot.

[0039] In step (2), the Zn-Cu alloy ingot is homogenized in a resistance furnace at 200-300℃ for 24 hours.

[0040] In step (2), after homogenization, the surface of the Zn-Cu alloy ingot is removed by sanding with sandpaper or a grinding wheel to remove oxidation and dirt, followed by acidification, and then hot-dip galvanizing. Specifically, the Zn-Cu alloy ingot is immersed in a zinc plating solution at 220-330℃ for 10-15 minutes. The zinc plating solution consists of ZnO, NaOH, and water, with a pH of 8-10.

[0041] In step (2), the process parameters for rotary forging are: temperature 100-300℃, cone feed angle 10°-21.67°, friction coefficient 0.1-0.3, axial feed speed 3-20mm / s, deformation per pass 20%-40%, and 2-3 passes.

[0042] (3) Performance testing

[0043] The tensile test was conducted according to the standard ASTM E8-2015a and was performed on an electronic universal testing machine of model 1NSTRON 5982.

[0044] The tensile fracture morphology of zinc-copper alloy bars was analyzed using a scanning electron microscope (SEM) model JSM-6700.

[0045] The testing instrument was a ZENNIUM™ 6 electrochemical workstation. The simulated body fluid used in the electrochemical experiment was SBF solution with the pH adjusted to 7.4 to simulate the normal human body fluid environment.

[0046] The corrosion immersion test was conducted in strict accordance with the standard ASTM-G31-2004, and the static corrosion rate was measured using static weight loss test in accordance with the standard ASTM G31-72.

[0047] Unless otherwise specified, all methods used in this invention are conventional methods known to those skilled in the art, and all reagents and materials used are commercially available products, and all instruments used are conventional instruments known to those skilled in the art.

[0048] II. Methods

[0049] 2.1 Effect of Deformation Amount on Zn-Cu Alloy in Rotary Forging Process

[0050] Zn-Cu ingots (Zn-2Cu alloy, Zn-3Cu alloy, Zn-4Cu alloy) and 2% calcium carbonate were melted at 500℃ to obtain a melt. A semi-continuous casting process was used to cast the melt, yielding Zn-Cu alloy ingots. The Zn-Cu alloy ingots were then cut into approximately 500 mm lengths using a saw. The Zn-Cu alloy ingots were then homogenized in a resistance furnace at 300℃ for 24 hours to eliminate component segregation and casting stress in the as-cast alloy. The homogenized Zn-Cu alloy ingots were then machined to produce alloy ingots with a diameter of 20 mm and a length of 10 mm. The Zn-Cu alloy ingots were then subjected to radial high-frequency short-stroke forging using three dies rotating at high speed around them. The forging temperature was 300℃, the conical feed angle was 10.5°, the friction coefficient was 0.1, the axial feed speed was 3 mm / s, the deformation per pass was 20%-40%, and the forging was performed in three passes.

[0051] 2.1.1 The total deformation and corresponding mechanical properties are shown in Table 1, and the stress-strain curves are shown in Table 1. Figure 1 As shown.

[0052] Table 1. Room temperature tensile mechanical properties of zinc-copper alloy bars with different deformation amounts

[0053]

[0054] It can be seen that the zinc-copper alloy with zero deformation exhibits low yield strength, tensile strength, and elongation at break. As the deformation increases to 84%, these properties significantly improve. When the deformation increases to 98%, the yield strength and tensile strength decrease, while the elongation at break increases. In summary, with increasing deformation, the yield strength and tensile strength of the zinc-copper alloy first increase and then decrease, while the elongation at break continuously increases. Furthermore, within the deformation range of 64%-98%, all yield strength, tensile strength, and elongation at break significantly improve, reaching their optimal strength at a total deformation of 84%. Moreover, for zinc-copper alloys with different Cu additions, using Zn-2Cu alloy as the initial ingot, the yield strength, tensile strength, and elongation at a total deformation of 84% all fall within an optimal range.

[0055] 2.1.2 To investigate the effects of different deformation amounts and copper content on the tensile fracture mode of zinc-copper alloys, the tensile fracture surfaces obtained after room temperature stretching were observed under a scanning electron microscope in secondary electron mode. The fracture morphologies of Zn-2Cu alloy bars with deformation amounts of 36%, 64%, and 84% are shown in the figure. Figure 2 As shown; the fracture morphologies of Zn-4Cu bars with deformation amounts of 36%, 64%, and 84% are as follows. Figure 3 As shown. From Figure 2-3It can be seen that the microstructure of the fracture surface becomes finer with increasing deformation. As the deformation increases, due to grain refinement, the brittle fracture (cleavage fracture) transforms into ductile fracture. When the deformation exceeds 64%, the bar exhibits ductile fracture characteristics such as dimples, indicating that the alloy begins to possess good plastic deformation capacity.

[0056] 2.1.3 To evaluate the corrosion resistance of Zn-2Cu alloys with different deformation amounts, three states of bars with deformation amounts of 36%, 64%, and 84% prepared by rotary forging of Zn-2Cu alloy were subjected to electrochemical experiments in simulated body fluid (SBF solution, pH=7.4) to study their corrosion behavior.

[0057] Figure 4 The figure shows the electrodynamic polarization curves of pure zinc and zinc-copper alloys with different deformation amounts in simulated body fluid after rotary forging. As can be seen from the figure, the potential of the Zn-2Cu alloy changes significantly with different deformation amounts. When the deformation amount is 36%, the Zn-2Cu alloy is slightly shifted towards a positive potential compared to pure zinc. When the deformation amount is 64%, the Zn-2Cu alloy is basically the same as pure zinc. When the deformation amount is 84%, the Zn-2Cu alloy shifts towards a negative potential compared to pure zinc.

[0058] Table 2 shows the fitting results of the polarization curves of zinc-copper alloys with different deformation amounts in simulated body fluid. As can be seen from Table 2, the corrosion rates of Zn-2Cu alloys with deformation amounts of 84% and 64% are 52.27 μm / year and 54.95 μm / year, respectively; the Zn-2Cu alloy with the worst corrosion resistance is the one with a deformation amount of 36%.

[0059] Table 2 Corrosion data of zinc-copper alloys with different deformation amounts in simulated body fluids.

[0060]

[0061] The conclusions are as follows: Zn-2Cu alloy corrodes faster than pure Zn. The corrosion potentials of the three metals in simulated body fluid range from -1.184 to -1.153, with little difference. As the deformation increases, the corrosion current density and corrosion rate of the zinc-copper alloy decrease. After the deformation reaches 64%, the corrosion rate of the Zn-2Cu alloy decreases significantly.

[0062] 2.1.4 The surface morphology of the Zn-2Cu alloy sample after immersion for 3 days was scanned and analyzed. The corrosion morphology image is shown below. Figure 5 As shown.

[0063] It can be seen that after immersing Zn-2Cu alloy samples with different deformation amounts in SBF for 3 days, the surfaces of the alloy samples in each state underwent varying degrees of corrosion. Furthermore, the uniformity of corrosion improved with increasing deformation amount, and the uniformity of corrosion significantly improved after the deformation amount reached 64%. Meanwhile, the corrosion resistance of the samples decreased after the addition of Cu.

[0064] 2.2 Influence of other factors on Zn-Cu alloys

[0065] 2.2.1 Effect of Zn-Cu alloy ingot preparation on Zn-Cu alloy

[0066] Zn-2Cu ingots and 2% calcium oxide were melted at 500℃ to obtain a melt, which was then cast using a semi-continuous casting process to obtain Zn-2Cu(CaO) alloy ingots. The Zn-2Cu(CaO) alloy ingots, Zn-2Cu ingots, and Zn-2Cu-0.2Ca alloy ingots were cut into approximately 500 mm lengths using a sawing machine. The three metals were then homogenized in a resistance furnace at 300℃ for 24 hours. After homogenization, the three metals were machined to produce alloy ingots with a diameter of 20 mm and a length of 10 mm. Three dies were used to simultaneously apply radial high-frequency short-stroke forging to the three metals at high speed. The forging temperature was 300℃, the conical feed angle was 10.5°, the friction coefficient was 0.1, the axial feed speed was 3 mm / s, the deformation per pass was 20%-40%, and the forging was performed in 3 passes, with a total deformation of 84%. The detected composition of the four metals is shown in Table 3, and the corresponding mechanical properties are shown in Table 4.

[0067] Table 3 Metal Detected Components

[0068]

[0069] Table 4. Room temperature tensile mechanical properties of zinc-copper alloy bars with different additives

[0070]

[0071] As can be seen from Table 3-4, the tensile properties of zinc-copper alloys decrease significantly with the addition of Ca, and the yield strength, tensile strength and elongation at break of zinc-copper alloys decrease continuously with the increase of Ca content.

[0072] Electrochemical experiments were conducted on the four zinc-copper alloy rods in simulated body fluid (SBF solution) to study their corrosion behavior. Table 5 shows the fitting results of the polarization curves of the zinc-copper alloys in simulated body fluid. It can be seen that both Cu and Ca accelerate the corrosion and degradation of the zinc alloys.

[0073] Table 5 Corrosion data of zinc-copper alloy rods with different additives in simulated body fluid.

[0074]

[0075] The surface morphology of four zinc-copper alloy samples after immersion for 3 days was scanned and analyzed. The corrosion morphology images are shown below. Figure 6 As shown, the corrosion uniformity is: Zn-2Cu(CaCO3) > Zn-2Cu-0.2Ca > Zn-2Cu > Zn-2Cu(CaO). Different degrees of corrosion occurred on the surfaces of the alloy samples in each state, with more pronounced corrosion at grain boundaries and phase boundaries. The corrosion uniformity of the Zn-2Cu alloy with added CaCO3 was better than that of the Zn-2Cu alloy with added CaO. This is presumably because CaCO3 has high stability and is less prone to decomposition or agglomeration during alloy preparation (such as smelting and casting), making it more likely to be distributed in the matrix as fine, uniform particles. Its interfacial bonding with the matrix is ​​more stable, resulting in a weaker "local triggering" effect on corrosion. In contrast, CaO, due to its high reactivity, may agglomerate or segregate during alloy preparation or service due to localized high temperatures or moisture, or form unstable interfacial phases (such as calcium oxides / salts) with zinc and copper in the matrix. This makes the interface a weak point where corrosion preferentially occurs, further compromising corrosion uniformity.

[0076] 2.2.2 Effect of Pretreatment on Zn-Cu Alloy

[0077] Zn-2Cu alloy ingots and 2% calcium carbonate were melted at 500℃ to obtain a melt, which was then cast using a semi-continuous casting process to obtain Zn-Cu alloy ingots. The Zn-2Cu alloy ingots were cut into approximately 500 mm lengths using a saw. The Zn-2Cu alloy ingots were then homogenized in an electric resistance furnace at 300℃ for 24 hours. After homogenization, the Zn-2Cu alloy ingots were polished with sandpaper or a grinding wheel to remove oxidation and dirt from the surface, followed by acidification (10wt% HCl). The surface of the Zn-Cu alloy ingots was then hot-dip galvanized (the galvanizing solution consisted of ZnO, NaOH, and water, with a mass ratio of ZnO:NaOH = 1:1, pH = 10, 270℃, time 10 min). After cleaning, the ingots were machined to produce alloy ingots with a diameter of 20 mm and a length of 10 mm. Three dies are used to simultaneously apply radial high-frequency short-stroke forging to the coated alloy ingot at high speed. The forging temperature is 300℃, the conical feed angle is 10.5°, the friction coefficient is 0.1, the axial feed speed is 3mm / s, the deformation per pass is 20%-40%, there are 3 passes, and the total deformation is 0%-84%. The coating detection and analysis are as follows:

[0078] Table 6. Analysis of Coating on Zinc-Copper Alloy Rods

[0079]

[0080] Table 7. Room temperature tensile mechanical properties of coated zinc-copper alloy bars

[0081]

[0082] As shown in Table 7, the yield strength, tensile strength, and elongation at break of the coated zinc-copper alloy are all improved, and the trend is basically the same as that of the zinc alloy in 2.1.1. With the increase of deformation, the yield strength and tensile strength of the zinc-copper alloy first increase and then decrease, while the elongation at break continues to increase. Furthermore, within the deformation range of 64%-98%, the yield strength, tensile strength, and elongation at break all significantly improve. Moreover, the coating can mask minor defects on the Zn-2Cu substrate surface (such as casting marks and scratches), resulting in more uniform grain size during rotary forging. Simultaneously, due to its chemical stability, it is not prone to blackening, allowing the zinc-copper alloy to maintain a smooth and uniform appearance over a long period.

[0083] Electrochemical experiments were conducted on zinc-copper alloy rods with coatings in simulated body fluid (SBF solution, pH=7.4). The fitting results of the polarization curves in the simulated body fluid are shown in Table 8. It can be seen that the coating slows down the corrosion and degradation of zinc alloy, but it can effectively prevent pitting corrosion and crevice corrosion. When the deformation reaches 64%, the corrosion rate of the alloy decreases significantly, and the corrosion rate reaches its lowest point when the deformation reaches 84%.

[0084] Table 8 Corrosion data of coated zinc-copper alloy rods in simulated body fluids.

[0085]

[0086] Furthermore, the etched zinc-copper alloy rods with coating, the etched zinc-copper alloy rods (section 2.1.3), and pure Zn-2Cu (deformation amounts of 36%, 64%, and 84%, respectively) were ground and subjected to microhardness testing using a Nanbei HVS-30T Vickers hardness tester. A test force of 10 kgf was set, and the measurement was initiated and held for 15 seconds. Six Vickers hardness values ​​were measured for each sample, and the average value was taken. The hardness results are shown in Table 9, indicating that the zinc oxide component in the coating has high microhardness and a dense structure, significantly improving the wear resistance of the alloy surface.

[0087] Table 9 Hardness of different zinc-copper alloy rods

[0088]

[0089] In summary, the Zn-Cu alloy prepared by the process described in this invention has good application prospects in the preparation of bioactive implantable devices. Considering the above-mentioned mechanical properties, electrochemical properties, and corrosion properties, the Zn-Cu zinc alloy has good application prospects in the preparation of bioactive implantable devices and bioactive membranes / patches, especially the Zn-2Cu(CaCO3+coating)-84% zinc alloy. Orthopedic implantable devices include, but are not limited to, bone plates, bone screws, bone tissue repair scaffolds, intramedullary nails, bone sheaths, or spinal fixation devices; bioactive membranes include at least one of guided bone regeneration membranes, guided tissue regeneration membranes, or oral barrier membranes; and bioactive patches include at least one of hernia patches or fistula patches.

[0090] The embodiments described above are merely examples of several implementations of the present invention, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the present invention. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of the present invention, and these modifications and improvements all fall within the scope of protection of the present invention.

Claims

1. A process for the preparation of Zn-Cu alloy based on regulating the amount of deformation, characterized by, The Zn-Cu alloy is used for a biodegradable medical Zn-Cu alloy, and the preparation process comprises the following steps: (1) Zn-Cu ingot blank and calcium carbonate are melted at a temperature of 450-500 DEG C to obtain a melt, and a semi-continuous casting process is used for casting to obtain a Zn-Cu alloy ingot; (2) After homogenization treatment of the Zn-Cu alloy ingot, the Zn-Cu alloy ingot is spin forged, the temperature is 100-300 DEG C, the pass deformation is 20-40%, the pass is 2-3 times, the total deformation of spin forging is 64%-98%, and the Zn-Cu alloy is obtained.

2. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 1, characterized in that, In step (1), the Zn-Cu ingot blank is one of Zn-2Cu alloy, Zn-3Cu alloy and Zn-4Cu alloy.

3. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 1, characterized in that, In step (1), the amount of calcium carbonate is 2%-4% of the mass of the Zn-Cu ingot blank.

4. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 1, characterized in that, In step (2), the Zn-Cu alloy ingot is homogenized in a resistance furnace, the homogenization treatment process is 200-300 DEG C, and the time is 24h.

5. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 1, characterized in that, In step (2), after homogenization treatment, the surface of the Zn-Cu alloy ingot is polished to remove oxidation and dirt, and then acidized, and hot-dip galvanizing is carried out on the surface of the Zn-Cu alloy ingot.

6. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 5, characterized in that, The hot-dip galvanizing is specifically that the Zn-Cu alloy ingot is immersed in a galvanizing liquid, the temperature is 220-330 DEG C, and the time is 10-15min.

7. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 6, characterized in that, The galvanizing liquid is composed of ZnO, NaOH and water, and the pH is 8-10.

8. The process for preparing Zn-Cu alloy based on regulating the amount of deformation according to claim 1, characterized in that, In step (2), the process parameters of the spin forging are as follows: the conical feeding angle is 10 DEG -21.67 DEG, the friction coefficient is 0.1-0.3, and the axial feeding speed is 3-20mm / s.

9. The application of the alloy prepared by the Zn-Cu alloy preparation process based on the controlled deformation amount according to any one of claims 1-8 in the preparation of biologically active implant devices, including the preparation of orthopedic implant devices and biologically active membranes / patches.

10. Use according to claim 9, characterized in that, The orthopedic implant devices include at least one of bone plates, bone screws, bone tissue repair scaffolds, intramedullary needles, bone setting sleeves or spinal internal fixation devices; the biologically active membranes include at least one of guided bone regeneration membranes, guided tissue regeneration membranes or oral barrier membranes, and the biologically active patches include at least one of hernia patches or fistula patches.

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